Interactions of Apolipoproteins AI, AII, B and HDL, LDL, VLDL with Polyurethane and Polyurethane-PEO Surfaces.

The lipoproteins (HDL, LDL, VLDL) are important components of blood present in high concentration. Surprisingly, their role in blood-biomaterial interactions has been largely ignored. In previous work apolipoprotein AI (the main protein component of HDL) was identified as a major constituent of protein layers adsorbed from plasma to biomaterials having a wide range of surface properties, and quantitative data on the adsorption of apo AI to a biomedical grade polyurethane were reported. In the present communication quantitative data on the adsorption of apo AI, apo AII and apoB (the latter being a constituent of LDL and VLDL), as well as the lipoprotein particles themselves (HDL, LDL, VLDL), to a biomedical segmented polyurethane (PU) with and without an additive containing poly(ethylene oxide) (material referred to as PEO) are reported. Using radiolabeled apo AI, apo AII, and apoB, adsorption levels on PU from buffer at a protein concentration of 50 µg/mL were found to be 0.34, 0.40, and 0.14 µg/cm(2) (12, 23, and 0.25 nmol/cm(2)) respectively. Adsorption to the PEO surface was <0.02 µg/cm(2) for all three apolipoproteins demonstrating the strong protein resistance of this material. In contrast to the apolipoproteins, significant amounts of the lipoproteins were found to adsorb to the PEO as well as to the PU surface. X-ray photoelectron spectra, following exposure of the surfaces to the lipoproteins, showed a strong phosphorus signal, confirming that adsorption had occurred. It therefore appears that a PEO-containing surface that is resistant to apolipoproteins may be less resistant to the corresponding lipoproteins.

Deterioration of polyamino acid-coated alginate microcapsules in vivo.

The implantation of immuno-isolated recombinant cell lines secreting a therapeutic protein in alginate microcapsules presents an alternative approach to gene therapy. Its clinical efficacy has recently been demonstrated in treating several genetic diseases in murine models. However, its application to humans will depend on the long-term structural stability of the microcapsules. Based on previous implantations in canines, it appears that survival of alginate-poly-L-lysine-alginate microcapsules in such large animals is short-lived. This article reports on the biological factors that may have contributed to the degradation of these microcapsules after implantation in dogs. Alginate microcapsules coated with poly-L-lysine or poly-L-arginine were implanted in subcutaneous or intraperitoneal sites. The retrieved microcapsules showed a loss of mechanical stability, as measured by resistance to osmotic stress. The polyamino acid coats were rendered fragile and easily lost, particularly when poly-L-lysine was used for coating and the intraperitoneal site was used for implantation. Various plasma proteins were associated with the retrieved microcapsules and identified with western blotting to include Factor XI, Factor XII, prekallikrein, HMWK, fibrinogen, plasminogen, ATIII, transferrin, alpha-1-antitrypsin, fibronectin, IgG, alpha-2-macroglobulin, vitronectin, prothrombin, apolipoprotein A1, and particularly albumin, a major Ca-transporting plasma protein. Complement proteins (C3, Factor B, Factor H, Factor I) and C3 activation fragments were detected. Release of the amino acids from the microcapsule polyamino acid coats was observed after incubation with plasma. indicating the occurrence of proteolytic degradation. Hence, the loss of long-term stability of the polyamino acid-coated alginate microcapsules is associated with activation of the complement system, degradation of the polyamino acid coating, and destabilization of the alginate core matrix, probably through loss of calcium-mediated ionic cross-linking of the guluronic acid polymers in the alginate. These destructive forces may be slightly mitigated by using poly-L-arginine instead of poly-L-lysine for coating and by implanting in a subcutaneous instead of an intraperitoneal site. However, the long-term stability of such devices may require significant improvements in the microcapsule polymer chemistry to withstand such biological impediments.

Towards practical soft X-ray spectromicroscopy of biomaterials.

Scanning transmission X-ray microscopy (STXM) is being developed as a new tool to study the surface chemical morphology and biointeractions of candidate biomaterials with emphasis on blood compatible polymers. STXM is a synchrotron based technique which provides quantitative chemical mapping at a spatial resolution of 50 nm. Chemical speciation is provided by the near edge X-ray absorption spectral (NEXAFS) signal. We show that STXM can detect proteins on soft X-ray transparent polymer thin films with monolayer sensitivity. Of great significance is the fact that measurements can be made in situ, i.e. in the presence of an overlayer of the protein solution. The strengths, limitations and future potential of STXM for studies of biomaterials are discussed.

Surface analysis methods for characterizing polymeric biomaterials.

Surface properties have an enormous effect on the success or failure of a biomaterial device, thus signifying the considerable importance of and the need for adequate characterization of the biomaterial surface. Microscopy techniques used in the analysis of biomaterial surfaces include scanning electron microscopy, transmission electron microscopy, atomic force microscopy, and confocal microscopy. Spectroscopic techniques include X-ray photoelectron spectroscopy, Fourier Transform infrared attenuated total reflection and secondary ion mass spectrometry. The measurement of contact angles, although one of the earlier techniques developed remains a very useful tool in the evaluation of surface hydrophobicity/hydrophilicity. This paper provides a brief, easy to understand synopsis of these and other techniques including emerging techniques, which are proving useful in the analysis of the surface properties of polymeric biomaterials. Cautionary statements have been made, numerous authors referenced and examples used to show the specific type of information that can be acquired from the different techniques used in the characterization of polymeric biomaterials surfaces.

Fluorinated surface-modifying macromolecules: modulating adhesive protein and platelet interactions on a polyether-urethane.

Polyether-urethanes (PEUs) have been the materials of choice for the manufacture of conventional blood-contacting devices. Nevertheless, biostability and blood compatibility are still among the principal limitations in their long-term application. Studies investigating the development of protective coatings for PEUs have shown that degradation can be reduced with the use of fluorinated surface-modifying macromolecules (SMMs). It has also been hypothesized that SMM-modified PEU surfaces may exhibit improved blood compatibility because other studies have shown a modulation in fibrinogen adsorption onto these surfaces. To determine the blood compatibility of a PEU-containing fluorinated SMMs, a series of in vitro experiments were designed to study the pattern of protein adsorption from plasma and then to assess the nature of platelet adhesion and activation on each substrate. Western blot analysis as well as single protein studies revealed that the dominant "adhesive proteins" [fibrinogen (Fg), fibronectin (Fnc), and vitronectin (Vnc)] were adsorbed on two of the SMM-containing PEUs in lower amounts relative to unmodified base. Platelet adhesion and activation data further highlighted the differences among the various substrates. It was shown that the unmodified base had a higher number of adhered platelets relative to the SMM-modified surfaces, and that of the SMM-containing substrates, which showed the lowest levels of adhesive proteins also, exhibited significantly lower platelet densities. Close morphological examination further revealed that platelets residing on these latter substrates were not appreciably activated. Based on the current evidence, it is believed that the fluorinated SMMs demonstrate good potential for the development of surfaces with minimal thrombogenic character in in vivo applications.

Protein adsorption to polyethylene glycol modified liposomes from fibrinogen solution and from plasma.

Unmodified and polyethylene glycol (PEG) modified neutral and negatively charged liposomes were prepared by freeze-thaw and extrusion followed by chromatographic purification. The effects of PEG molecular weight (PEG 550, 2000, 5000), PEG loading (0-15 mol%), and liposome surface charge on fibrinogen adsorption were quantified using radiolabeling techniques. All adsorption isotherms increased monotonically over the concentration range 0-3 mg/ml and adsorption levels were low. Negatively charged liposomes adsorbed significantly more fibrinogen than neutral liposomes. PEG modification had no effect on fibrinogen adsorption to neutral liposomes. An inverse relationship was found between PEG loading of negatively charged liposomes and fibrinogen adsorption. PEGs of all three molecular weights at a loading of 5 mol% reduced fibrinogen adsorption to negatively charged liposomes. Protein adsorption from diluted plasma (10% normal strength) to four different liposome types (neutral, PEG-neutral, negatively charged, and PEG-negatively charged) was investigated using gel electrophoresis and immunoblotting. The profiles of adsorbed proteins were similar on all four liposome types, but distinctly different from the profile of plasma itself, indicating a partitioning effect of the lipid surfaces. alpha2-macroglobulin and fibronectin were significantly enriched on the liposomes whereas albumin, transferrin, and fibrinogen were depleted compared to plasma. Apolipoprotein AI was a major component of the adsorbed protein layers. The blot of complement protein C3 adsorbed on the liposomes suggested that the complement system was activated.

Modification of liposomes with N-substituted polyacrylamides: identification of proteins adsorbed from plasma.

Liposomes prepared from DMPC (80%) and cholesterol (20%) were modified with a series of hydrophobically modified N-substituted polyacrylamides, namely, poly[N-isopropylacrylamide] (PNIPAM), poly[N,N-bis(2-methoxyethyl) acrylamide] (PMEAM), and poly[(3-methoxypropyl)acrylamide] (PMPAM). The hydrophobic group, N-[4-(1-pyrenylbutyl)-N-n-octadecylamine was attached to one end of the polymer chains to serve as an anchor for incorporation into the liposome bilayer. Liposome-polymer interactions were confirmed using fluorescence spectroscopy and chemical analysis. Microscopy revealed differences in aggregation tendency between unmodified and polymer-modified liposomes. Proteins adsorbed to liposome surfaces during exposure to human plasma were identified by immunoblot analysis. It was found that both unmodified and polymer-modified liposomes adsorb a wide variety of plasma proteins. Contact phase coagulation proteins, complement proteins, cell-adhesive proteins, serine protease inhibitors, plasminogen, antithrombin III, prothrombin, transferrin, alpha(2)-microglobulin, hemoglobin, haptoglobin and beta-lipoprotein as well as the major plasma proteins were all detected. Some differences were found between the unmodified and polymer-modified liposomes. The unmodified liposomes adsorbed plasminogen mainly as the intact protein, whereas on the modified liposomes plasminogen was present in degraded form. Also, the liposomes modified with PNIPAM in its extended conformation (below the lower critical solution temperature) appeared to adsorb less protein than those containing the 'collapsed' form of PNIPAM (above the LCST).

Adsorption from plasma and buffer of single- and two-chain high molecular weight kininogen to glass and sulfonated polyurethane surfaces.

The adsorption of high molecular weight kininogen (HK) in its single-chain (SCHK) and two-chain (TCHK) forms from single protein solutions, plasma, and kininogen-deficient plasma, to glass and sulfonated polyurethane surfaces is reported. Using radiolabelling methods, it was found that in a single protein buffered system there was no difference in the adsorbed amounts of SCHK and TCHK over the concentration range 5-100 microg ml(-1) (similar to that in plasma). The adsorption of the two forms from normal plasma was also the same. However, immunoblots using an anti-HK antibody indicated that over the 2 h adsorption time, much of the SCHK present in the plasma was converted to TCHK: the band at 120 kD representative of intact SCHK disappeared, and bands at 56 and 46 kD representative of the heavy and light chains of TCHK were generated. To prevent conversion of SCHK to TCHK, the kallikrein inhibitor aprotinin (or in some cases a protease inhibitor cocktail), was added to the plasma in subsequent experiments. In addition, kininogen-deficient plasma was used (with either labelled SCHK or TCHK added) to avoid ambiguity in the tracer-population relationship. It was again found that there was no difference in the amounts of SCHK and TCHK adsorbed to glass and the sulfonated polyurethanes. The significance of these findings in relation to the reported anti-cell adhesion properties of adsorbed HK is discussed.

Immunoblot analysis of proteins associated with HEMA-MMA microcapsules: human serum proteins in vitro and rat proteins following implantation.

Human serum proteins and their fragments, associated with hydroxyethyl methacrylate-methyl methacrylate (HEMA-MMA) copolymer microcapsules, were characterized using sodium dodecyl sulphate-polyacrylamide gel electrophoresis (SDS-PAGE) and immunoblot analysis. Capsules were incubated with serum for 1 week in vitro and then dissolved in ethanol to also precipitate the adsorbed protein. The precipitate was dissolved in 2% (w/v) SDS (the 'capsule eluate') to be assayed by electrophoresis. The majority of proteins probed for in the immunoblots were detected in the capsule eluates. These included fibronectin, plasminogen, IgG, vitronectin, Factor B, Factor H, Factor I, C3, but not beta-lipoprotein, fibrinogen, HMWK, or IgM. Complement activation fragments were detected in both the immunoblots of the capsule eluates and the medium containing serum without capsules. Thus, the adsorption of these fragments, formed independent of capsule presence, may be partially or completely responsible for the complement fragments associated with capsules. The prevention of complement activation by the addition of 5.8 mM EDTA, at the beginning of the week-long incubation, resulted in fewer low-molecular-weight C3 fragments associated with capsules. Rat proteins were also detected in immunoblots of the eluate of 'free-floating' capsules from the rat peritoneal cavity following implantation for 1 day using anti-human antibodies. Detected proteins included HMWK, fibrinogen, antithrombin III, transferrin, alpha1-antitrypsin, fibronectin, albumin, alpha2-macroglobulin, vitronectin, beta2-microglobulin, Factor B and Factor I. Rat fibrinogen, IgG, and complement C3 fragments were also detected in these immunoblots, but with monoclonal antibodies against the rat proteins.

Effect of single-chain and two-chain high molecular weight kininogen on adsorption of fibrinogen from binary mixtures to glass and sulfonated polyurethane surfaces.

The adsorption of fibrinogen from a single protein solution and from binary mixtures of fibrinogen and high-molecular-weight kininogen (HK) to glass and four sulfonated polyurethane surfaces is reported. The effect of the single-chain (SCHK) and two-chain (TCHK) forms of HK on fibrinogen adsorption was investigated. Using radiolabeling methods, fibrinogen adsorption from a series of mixtures having the same weight ratio of fibrinogen to HK as in plasma (50:1), but varying in total concentration, was measured. Fibrinogen adsorption from the mixtures was reduced on all surfaces compared to the single-protein solution, confirming the highly surface-active nature of this protein. However, except for glass, there was no significant difference between the SCHK and TCHK forms. Polyacrylamide gel electrophoresis and immunoblotting analysis of the proteins eluted from the surfaces after contact with the fibrinogen-SCHK solutions indicated that although intact SCHK was essentially conserved, some transformation of SCHK to TCHK on the surface occurred during the course of the experiment. It is hypothesized that in purified form, in which HK is not complexed to prekallikrein or factor XI, the surface-binding domain is more available than in the complexed forms which are present in plasma. If so, then the removal of bradykinin by kallikrein, as occurs in generating TCHK, may not be required for the expression of surface-binding domain activity.

Adsorption of immunoglobulin G and anti-factor VIII inhibitory antibody from haemophiliac plasma to derivatized polystyrenes.

Modified polystyrene resins containing sulphonate groups and tyrosyl sulphamide or tyrosyl methyl ester sulphamide groups have been investigated with respect to their potential for selective binding of anti-Factor VIII inhibitory antibodies from plasma. Adsorption of total immunoglobulin G and of a monoclonal antibody to Factor VIII was measured following addition of the radioiodinated proteins to normal plasma, plasma depleted of Factor VIII by adsorption on a resin coupled to anti-Factor VIII antibody, and haemophiliac plasma containing various levels of inhibitory anti-Factor VIII antibody. Depletion of anti-Factor VIII antibody from the haemophiliac plasmas by incubation with the resins was also measured by Bethesda assay. The modified resins and their corresponding unmodified "controls' showed similar binding of total immunoglobulin G. However, only resins containing either sulphonate or a combination of sulphonate and tyrosyl sulphamide groups showed evidence of selective adsorption of anti-Factor VIII antibody from plasma.

Identification of proteins absorbed to hemodialyser membranes from heparinized plasma.

The protein layers formed during contact of plasma with hemodialysis membranes were studied. Dialysers having membranes of cellulose acetate (CA), saponified cellulose ester (SCE), cuprophane (CUP), polymethylmethacrylate (PMMA), and polyacrylonitrile (PAN) were used. Heparinized human plasma was recirculated through the dialysers for four hours. They were then rinsed and the proteins adsorbed to the membranes were eluted with 2% SDS. The yields of protein from the different membranes increased in the order: PMMA < CA < SCE < CUP < PAN. This is the probable order of increasing hydrophilicity. SDS-PAGE and Western blots were performed on the dialyser eluates. The blots were positive for most of the twenty proteins tested for. There were some interesting differences in adsorption patterns among the different membrane materials, notably for high molecular weight kininogen (HMWK), plasminogen and the C3 component of complement. HMWK was intact in the eluates from CA, CUP and SCE, whereas on PMMA and PAN there was evidence of cleavage, suggesting that activation of the contact phase of coagulation was more extensive on the latter two materials. Intact plasminogen was visible on all the blots. However, low molecular weight fragments were visible in the PAN eluates, suggesting activation of the fibrinolytic pathway. Low molecular weight fibrinogen fragments eluted from PAN membranes support this conclusion. C3 was visible in the blots obtained for all membrane materials, and the data suggest that complement is activated by all the membranes. A C3 fragment at about 30 kD (possibly C3d) was seen in the blots for the cellulosic membranes but not for PMMA or PAN.

Delivery of passivating proteins to sutures during passage through the vessel wall reduces subsequent platelet deposition by blocking fibrinogen adsorption.

Intraluminal vascular suture material, which attracts fewer than the expected number of platelets compared with the same biomaterial exposed to blood in vitro, differs from the untreated biomaterial in that it has been passed once through the vessel wall. The mechanism by which this apparently trivial maneuver reduces platelet deposition was investigated. Polypropylene suture (7-0 Prolene) was passed through human arteries (fetal and adult), and platelet deposition to the suture was measured in a standardized perfusion chamber. Single vessel passage of the sutures reduced platelet deposition by 68 +/- 23%, which contrasts sharply with the power of prostaglandin E1 (1 microM PGE1 is sufficient to abolish platelet shape change and aggregation), which inhibited only 11% of platelet deposition to the sutures. Aspirin treatment of the vessel (to prevent PGI2 formation) or endothelial stripping (to remove the ability to produce nitric oxide) had no effect on the degree of inhibition. Passage of the suture through a vessel analogue (expanded polytetrafluoroethylene) did not inhibit platelet deposition. 125I-fibrinogen adsorption to the suture after vessel passage was reduced to a degree similar to that of platelet deposition. Sodium dodecyl sulfate-polyacrylamide gel electrophoresis of proteins eluted from vessel-passed sutures revealed bands at 66, 47, and 16 kd. Western blotting indicated the presence of large amounts of albumin and hemoglobin, a moderate amount of haptoglobin, and only trace amounts of fibrinogen. When sutures were exposed to each of these proteins in vitro before perfusion, albumin and hemoglobin were found to reproduce the effect of vessel passage alone on platelet deposition. We conclude that albumin and hemoglobin adsorb to sutures during their passage through the vessel subendothelium.(ABSTRACT TRUNCATED AT 250 WORDS)